Textile-based electrode

ABSTRACT

Textile-based electrodes include a fabric portion having stretch-recovery non-conductive yarns and an electrically conductive region having stretch-recovery electrically conductive yarn filaments. The electrodes can further include float yarns and can be configured in a textured or ribbed construction. When incorporated into a garment, the electrodes can be used to monitor biophysical characteristics, such as the garment wearer&#39;s heart rate. In addition, two garments with textile based electrodes are disclosed. First, a wrist band for use with a cardiac patient remote monitoring system includes two fabric layers with integral textile-based electrodes. The skin contacting surface of the band includes a conductive region formed as a continuous ring or stripe. A connector links the conductive region to a lead to a device. Second, an infant garment includes textile based electrodes at the torso region and optionally at other regions in order to monitor the infant&#39;s biophysical characteristics as the garment is worn.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a continuation of U.S. patent application Ser. No.11/672,742, filed Feb. 8, 2007, now U.S. Pat. No. 7,966,052, which is acontinuation-in-part of U.S. patent application Ser. No. 11/082,240,filed Mar. 16, 2005, now U.S. Pat. No. 7,308,294.

FIELD OF THE INVENTION

The invention relates to a textile-based electrode or electrode systemthat is incorporated into a garment or monitoring system, such as awrist band for remote monitoring of cardiac electrical activity and/orpacemaker function. Alternatively, such textile-based electrode orelectrode system may be incorporated into an infant garment or adultgarment.

BACKGROUND OF THE INVENTION

Textile-based electrodes consisting of electrically conductive wiressurrounded by a region of electrically nonconductive textile fibers canbe integrated with a wearable article, such as a garment. The wearablearticle can be adapted to receive or transmit electrical impulses to orfrom the wearer and, in turn, to or from an electrical device. Thepatent document WO 01/02052, assigned to Bekaert, discloses such awearable article.

Wearable textile-based sensors for sensing or otherwise reporting theheart rate (the pulse) of the wearer are disclosed in patent document WO02/071935, assigned to RTO Holding OY.

Patent document WO 03/094717, assigned to Koninklijke PhilipsElectronics NV, discloses a textile article that is provided with aregion of skin contacting electrodes that are fully integrated within atextile article. The disclosed textile article takes the form of a “braor a ladies top,” which is otherwise electrically nonconducting. Thearticle is provided with partially overlapping layers of electricallyconductive material and electrically insulative material arranged topartially cover and electrically isolate the electrically conductivematerial.

Patent document WO 2004/006700, assigned to Tefron Ltd., discloses acircularly knit garment having an inner surface electrically-conductiveregion disposed close to the wearer's skin. The innerelectrically-conductive region cooperates to conduct electrical signalsto an outerlying electrically-conductive region. Such electrical signalsmay include the heart rate coming from the wearer or anelectro-stimulation means going to the wearer.

Each of these patent documents relates an objective to provide anelectrically-conductive region, which can function as an electrodeintegrated with a garment, a belt, or other wearable article oftraditional textile construction. Generally, these patent documentsdisclose an electrically-conductive region that is otherwiseelectrically isolated from the remainder of the garment or wearable.Furthermore, these patent documents disclose placing at least oneelectrically-conductive region of the garment in close contact with theskin of the wearer. As a result, the electrode, formed by thiselectrically-conductive region in contact with the skin, provides apick-up point for electrical signals generated within the corpus of thewearer. Alternatively, such an electrode provides a point of contact onthe skin to receive an electrical signal generated externally to thewearer. In summary, these patent documents provide means to communicateelectrical signals to or from the corpus of a garment wearer.

In addition, these patent documents also generally disclose at least asecond textile electrode. More often, the second electrode is integratedwith the garment and located at or near an exterior surface of thegarment. The second electrode can also be advantageously placedoverlying the electrode in skin contact, while also having a portion ofthe garment's electrically insulating materials of constructiontherebetween. Where an electrical connection between the electrode(s) inskin contact and the exterior electrode(s) is desired, such connectioncan be established using metallic wires. Alternatively, the skin contactelectrode can be folded over in such a manner as to form the exteriorsurface electrode continuously.

Where an electrical connection between a garment-integrated electrode inskin contact with the wearer and a garment-integrated exterior electrodeis established using metallic wires, certain limitations may exist. Suchlimitations can be present, for example, when biophysical monitoring viaelectrical contact with the corpus is desired. These limitations, forexample, may include the difficulty of making metallic wires part of atraditionally fabricated textile due to the fragility and durableflexibility of metal wires.

Similarly, other configurations may suffer certain limitations. Forexample, configurations incorporating “folded over” and partiallyoverlapping layers of electrically conductive material (withelectrically insulative material arranged to electrically isolate theelectrically conductive material) may severely limit the freedom todesign the placement of electrodes integrated with a garment or textilearticle.

Remote monitoring systems for cardiac patients include a monitoring andtransmitting device that connects by telephone to a remote receivingstation. With such systems, a cardiac patient wears a wrist bandelectrode on each arm. The wrist band electrodes are electricallycoupled by ECG leads to the remote monitoring system to transmit apatient signal to the monitoring system, such as an electrocardiogram(ECG) signal or a pacemaker signal. The monitoring system frequentlyincludes a telephone with a phone cradle that has a speaker and amicrophone to facilitate telephonic voice communication as well assystem signal communication with the remote receiving station.Representative systems are shown in U.S. Pat. Nos. 5,586,556 and5,467,773. In alternative monitoring systems for cardiac patients,wrist-worn electrode devices emulate wrist watches and collect and storedata for later recovery by a health care professional directly from thedevice. Representative systems are shown in U.S. Pat. Nos. 4,120,294 and5,317,269. The wrist band electrodes in these current cardiac monitoringsystems are formed generally from stiff materials, such as metal, andare not always comfortable for patients. In addition, a conforming fitaround a patient's wrists improves data pick-up and transmission fromwrist-worn electrodes. Current electrode systems can be difficult toinstall over a patient's wrists to achieve desired conforming fit, andcan be difficult to wear.

Pediatric monitoring systems often engage electrodes directly to aninfant's skin via gel or adhesives. Such systems are used mostfrequently with tiny prematurely born infants, where the electrodes andleads extending therefrom can be difficult to apply and distressing foran infant's parents to view. More comfortable and more aesthetictextile-based electrode systems are sought for pediatric monitors.

Accordingly, there exists a need to provide textile-based electrodescapable of overcoming one or more of the deficiencies of the prior art.

SUMMARY OF THE INVENTION

The present invention provides a textile-based electrode or electrodesystem that can be incorporated in to a wearable article, such as agarment. The textile-based electrode can include a fabric portion havingstretch-recovery non-conductive yarns and an electrically conductiveregion having stretch-recovery electrically conductive yarn filaments.

The textile-based electrode system can include first and second fabricportions that include electrically conductive regions. The electricallyconductive regions can be disposed in a partially overlappingrelationship, allowing for a region of partial physical contact that canresult in electrical conduction between the electrically conductiveregions.

At least one of the electrically conductive regions can include a floatyarn. In addition, at least one of the electrically conductive regionscan be made up of an elastified electrically conductive yarn and/or anelastic yarn at least partially plated with a conductive yarn. In oneembodiment, the electrically conductive regions can include a fabrichaving a textured or ribbed construction. In further embodiments, theelectrically conductive regions can include a portion or portions havingat least one hydrophobic material and/or can be separated by a regionhaving at least one hydrophobic material.

Textile-based electrodes falling within the scope of the presentinvention can be connected to a measuring device. The measuring devicecan, for example, be used to monitor biophysical signals of a wearer ofa garment incorporating the electrodes. For instance, in one embodiment,the textile-based electrodes can be used to facilitate monitoring awearer's heart rate.

Further illustrative embodiments into which textile-based electrodes maybe incorporated include an infant monitoring garment for monitoringbiophysical characteristics and a wrist band for a cardiac patientmonitoring system. In the infant garment, the textile-based electrodesmay be incorporated into one or more bands formed at the torso region ofthe garment or alternatively into the sleeve or wrist of the garment.The wrist band may include a comfortable stretch-recovery knit, withportions of the skin contacting surface and the outer surface havingelectrically conductive fibers therein. Greater comfort is providedwhere the textile-based electrodes in the wrist band are formed fromstretch-recovery conductive yarn filaments.

BRIEF DESCRIPTIONS OF THE DRAWINGS

The present invention will be described in the following detaileddescription with reference to the following drawings:

FIGS. 1A and 1B are schematic representations of a top plain view and abottom plain view of a first textile-based electrode;

FIG. 1C is a schematic representation in side elevation of the firsttextile-based electrode of FIGS. 1A and 1B, comprising a portion ofelectrically conductive float yarns in contact with a portion ofelectrically conductive float yarns of a second textile-based electrodeof FIGS. 1D and 1E;

FIGS. 1D and 1E are schematic representations of a top plain view and abottom plain view of a second textile-based electrode;

FIG. 1F is a schematic representation of an integrated textile electrodecomprising a portion of electrically conductive region using differenttypes of knit construction;

FIGS. 2A and 2B are schematic representations of an upper body wearablearticle having textile-based electrodes;

FIG. 3A is a schematic representation in front plain view oftextile-based electrodes;

FIGS. 3B and 3C are schematic representations of the textile-basedelectrodes in folded configuration;

FIG. 4 is a schematic representation in partial cross-section of a pairof textile-based electrodes adapted to communicate with electronicscapable of biophysical monitoring;

FIG. 5 is schematic representation of a continuous band adapted towearing about the body and adapted for use with electronics capable ofbiophysical monitoring;

FIG. 6 is a schematic representation of a pair of textile-basedelectrodes and certain dimensions variable in their construction.

FIG. 7 is a top plan view of a pacemaker and heart monitoring andtransmitting device that includes wrist worn electrodes of thisinvention attached to the device by leads;

FIG. 8 is a top plan view of a wrist worn electrode of the inventionworn over a patient's wrist;

FIG. 9 is a top plan view of the wrist worn electrode of FIG. 8;

FIG. 10 is an enlarged fragmental cross-sectional view in elevationtaken along line 10-10 of FIG. 9;

FIG. 11 is a top plan view of a circular knit fabric into which a stripeand a patch of electrically conductive yarns has been knitted;

FIG. 12 is an enlarged fragmental cross-sectional view showing stitchingafter the fabric of FIG. 11 is folded to form the wrist worn electrode;

FIG. 13 is a front elevational view of a one piece outfit for an infantthat incorporates textile based electrodes in bands at the torso and atthe wrists;

FIG. 14 is a partial front elevational view of a one piece outfit for aninfant that incorporates textile based electrodes in bands at theankles;

FIG. 15 is a top plan view of an alternate embodiment of a wrist wornelectrode; and

FIG. 16 is a plan view of the inner or skin-contacting service of thewrist worn electrode, as seen upon inverting the wrist worn electrode ofFIG. 15.

DETAILED DESCRIPTION OF THE INVENTION

The present invention, in one embodiment, can provide a textile-basedelectrode capable of being fully integrated with a wearable article thatcan be adapted to allow contact of the electrode with the corpus of thewearer. The textile-based electrode disclosed herein is capable of beingadapted for the transmission of electrical signals to the wearer of anarticle integrated with the electrode. For example, such textile-basedelectrode may be adapted for the biophysiological monitoring of thewearer.

The textile-based electrode disclosed herein is also capable oftransmitting or receiving electrical signals via contact with the corpusof the wearer without relying on fragile connection wires. Thetextile-based electrode may also be specifically adapted for thereliable contact with corpus of the wearer, further providing relativelyconsistent electrical continuity with a complementary textile-basedelectrode (i.e., without signal loss or short circuiting while thewearer moves freely). In this regard, the textile-based electrode may bestretchable in the electrically conductive area due to the presence ofelastic materials that are knitted or woven with electrically conductiveyarns or filaments and/or through the use of yarns or filaments that areboth elastic and electrically conductive.

In one embodiment, the textile-based electrode can be included within anelectrode system comprising a first fabric portion provided with aportion of electrically conductive yarns in a knit construction. Theknit construction can, for example, be chosen from among single jersey,ribbed knit, mock ribbed knit, and ribbed knit 1×1 and 1×3constructions. The portion of electrically conductive yarns can besurrounded by, and electrically isolated from, the first fabric portion.

The textile-based electrode can exhibit stretchability in theelectrically conductive area due to the presence of a material, such asLycra® spandex, plated with a conductive yarn or filament. Thetextile-based electrode can also exhibit stretchability in theelectrically conductive area through the use of a conductive yarn, suchas the conductive yarns disclosed in WO 2004/097089A1 (assigned INVISTATechnologies S. à r. l.), the entire disclosure of which is incorporatedherein by reference. In addition, the textile-based electrode canexhibit stretchability by using different types of knit constructions,such as a ribbed construction (including, for example, 1×1 or 1×3 ribbedknit constructions).

In a further embodiment, a textile-based electrode is provided within anelectrode system, which comprises at least a first fabric portion and asecond fabric portion disposed in a partially overlying relationship.The first fabric portion may comprise at least a first electricallyconductive region (a first “electrode”) and the second fabric portionmay comprise at least a second electrically conductive region (a second“electrode”). The electrically conductive region of the first fabricportion and the electrically conductive region of the second fabricportion can cooperate to provide a region of partial physical contact.This physical contact region can thereby establish electrical conductionbetween the first and second “electrodes.”

The first and second electrically conductive regions or “electrodes”each comprise at least a portion of electrically conductive yarns. Inaddition, the first and second electrically conductive regions or“electrodes” may each further comprise at least a portion of “floatyarns.”

Embodiments falling within the scope of the present invention may befurther described with reference to the figures disclosed herein.

In one embodiment, a first textile-based electrode is provided within anelectrode system comprising a first fabric portion 10 that is providedwith a portion of electrically conductive yarn 30, as represented inFIGS. 1A and 1B. In this embodiment, the portion of electricallyconductive yarn 30 (FIG. 1A) is surrounded by and electrically isolatedfrom the first fabric portion 10.

A second textile-based electrode comprises a first fabric portion 20that is provided with a portion of electrically conductive yarns 40, asrepresented in FIGS. 1D and 1E.

In embodiments falling within the scope of the invention, a knitconstruction can be used. The knit construction may, for example, bechosen from among single jersey, mock ribbed knit, and ribbed knit 1×1and 1×3 constructions for both the fabric portion 10 and 20 and theconductive yarns 30 and 40. As is known to a person having skill in theart, in such knit fabrics, the wales, or vertical rows of stitches,typically intermesh alternately on the face (odd number wales) and onthe back (even number wales) of the fabric. Rib-knit fabrics of thistype have been shown to have good elasticity in the length and widthdirections and can provide good body form fitting garments.

A further embodiment of the invention provides for the conductive yarns30 and 40 to be knitted in with floats. Floats, as known to a personhaving skill in the art, comprise a portion of yarn that extends overthe fabric without being knitted in (i.e. floating or lying on thefabric surface). Fabric portions 10 and 20 with electrically conductiveyarns 30 and 40 in a rib-knit construction can provide atextile-electrode structure wherein yarns 30 and 40 are floated over theribbed structure of the fabric. As a result, these conductive floatyarns 34 and 44 (FIGS. 1A, 1B, 1D, and 1E) are readily accessible on thesurface of the fabric. The ready accessibility of the conductive floatyarns 34 and 44 facilitates electrical contact between the conductiveyarn portions of fabric through the physical contact of the float yarns.In one embodiment, the electrical contact between conductive yarnportions may be further facilitated by stitching conductive float yarns34 and 44 together.

As shown in FIG. 1C, the first textile-based electrode 15 and the secondtextile-based electrode 25 may be placed adjacent to one another,putting float yarns 34 and 44 in contact with one another to establishelectrical conductive contact.

Materials suitable for use as conductive yarns 30 and 40, and thus thefloat yarns 34 and 44, include, for example, those yarns disclosed inpatent document WO 20041097089A1 (assigned to the applicant INVISTATechnologies S. à. r. l.), the entire disclosure of which isincorporated herein by reference. The conductive yarns disclosed withinWO 2004/097089A1 (hereinafter called ETG1 yarns) can inherently provideelastic stretch and recovery and can lend themselves to knitconstructions for embodiments disclosed herein. Inelastic conductivefilaments suitable for preparing the elastic conductive yarns accordingto the disclosures in WO 2004/097089A1 include those yarns from BEKAERTFibre Technologies (such as CONDUFIL® 80 dtex and 24 filament yarns) andthose yarns known as Xstatic® yarns of a silver metallized nylon yarnfrom Laird Sauquoit Industries (Scranton, Pa., USA 18505).

Electrically nonconductive yarns or traditional textile yarns can beadvantageously employed for the bulk of the fabric portion. These yarnscan include, for example, cotton, cellulosics, silk, ramie, polyester,and/or nylon. The bulk of the fabric portion can also includecombinations of polyester and nylon with elastic yarns (such as LYCRA®branded spandex from INVISTA™ S. à r. l.).

In this regard, FIG. 1F shows a representation of an integrated textileelectrode 35 having a portion of an electrically conductive region 40′using different types of knit construction, including a ribbedconstruction (i.e. 1×1 or 1×3 rib). Such electrode can be within alarger region 18 surrounding the electrically conductive region 40′ andhaving, for example, a ribbed construction. The electrode area canstretch due to, for example, the presence of Lycra® spandex plated withthe conductive yarns, or through the use of an elastic conductive yarn,such as a yarn disclosed in WO 2004/097089A1 (ETG1). In addition,through the use of a ribbed construction and elastic materials, thestretch electrode can provide improved contact with the skin and hencebetter signal pick-up.

Such ribbed construction stretch electrodes can be made, for example, ona SMA-8-TOP1 seamless, 13 inch body size, knitting machine from SANTONI(from GRUPPO LONATI, Italy).

Examples of conductive yarns that can be used in such integrated textileelectrodes include Xstatic® 70 denier 2 ply (e.g. silver metallizednylon yarn of 70 denier and 34 filaments from Laird Sauquoit Industries(Scranton, Pa., USA 18505) and ETG1 yarns (hollow spindle double covered70 denier nylon yarn on LYCRA® Type 162 “clear” and 20 micron silverplated copper wire from Elektro Feindraht).

FIG. 1C shows an edgewise view of fabric portion 10 and fabric portion20 oriented about the axis extending from A to A′. As shown in thisfigure, physical contact can occur between yarn floats 34 in fabric 10and yarn floats 44 in fabric 20. This physical contact of floats 34 and44, or a plurality of similar floats, can provide electrical continuitybetween the fabric portions 10 and 20.

As represented in FIG. 10, when the conductive float yarn portion 34 offabric portion 10 is in contact with the conductive float yarn portion44 of fabric portion 20, the conduction of an electrical signal betweenthe two conductive yarn portions, i.e. from conductive portion 30 onsurface 12 to conductive portion 40 on surface 22, can be enabled.

An embodiment of a textile-based electrode system, fully integrated witha wearable article, such as a shirt, is represented with the aid ofFIGS. 2A and 2B. In these figures, a wearable 100 is represented as anupper body worn garment. The wearable 100 can be constructed usingcommonly practiced seamless (circular) knitting technology. In an“as-knitted” form using, for example, seamless technology, wearable 100takes the shape of a tube with upper 90 and lower 80 mirror imageportions about axis-AA′. The lower portion 80 in FIG. 2A, may be foldedinto the upper portion 90, to form a two ply garment having inner andouter portions, as represented in FIG. 2B. A waist band of a garment canbe constructed in a similar manner.

FIGS. 2A and 2B represent wearable 100 as having a textile-basedelectrode system of the invention fully integrated with it. The outersurface portion of the textile-based electrode system 40, is shown asbeing associated with lower portion 80. The outer surface portion of thetextile-based electrode system 40 is electrically continuous with innersurface portions 42 and with float yarns 44, shown with dashed lines.The outer surface portion of the textile-based electrode system 30, isshown as being associated with upper portion 90 and is electricallycontinuous with inner surface portions 32 and with float yarns 34, shownwith dashed lines. When lower portion 80 is folded into upper portion 90of wearable 100, float yarn portions 34 and 44 come into physicalcontact, as shown in FIG. 2B (in the manner as represented by FIG. 1C).As a result of the physical contact between portions 34 and 44, anelectrical signal can pass in either direction from electrode 30 on theouter surface of the two ply garment 100, to electrode 40 on the innersurface and thereon to the skin of the wearer.

Another embodiment of a textile-based electrode system is representedwith the aid of FIGS. 3A and 3B. In FIG. 3A a portion of a fabric 70,bounded by two horizontal axes, CC′ and BB′, is represented. A thirdhorizontal axis, AA′, placed equi-distant in a vertical direction fromboth CC′ and BB′, is also represented in FIG. 3A.

In FIGS. 3A and 3B, two textile-based electrodes are placed opposite oneanother in the horizontal direction. These electrodes include first andsecond outer portions of conductive yarns 30 and 30′, as represented inFIG. 3A. These electrodes further include inner conductive yarn portions34 and 34′, represented in FIG. 3A, using dashed lines to illustrate thefloat yarns lying directly under yarn portions 30 and 30′ respectively.

Similarly, FIG. 3A shows components of textile-based electrode systems,including third and forth outer portions of optional moisture retentiveyarns, such as cotton, 46 and 46′. Such electrode systems furtherinclude inner conductive yarn portions 44 and 44′, represented in FIG.3A using dashed lines to illustrate the float yarns lying directly underconductive yarn portions 40 and 40′ respectively. Conductive yarns 40and 40′, which are respectively continuous with 44 and 44′, andsurrounded by optional moisture retentive yarn portions 46 and 46′,respectively.

Further represented in FIG. 3A, is a metallic connector 50 adapted tofunction as central point for electrical connection to a textile-basedelectrode.

FIG. 3B is a representation of fabric portion 70 after folding alonghorizontal axis AA′ and causing axes CC′ and BB′ to meet co-linearlyalong a new horizontal axis CB-C′B′. As a result of making this fold infabric portion 70 along horizontal axis AA′, a two-ply fabric portion isformed. The inner conductive yarn portions and the associated float yarnportions, respectively 34 and 44 and 34′ and 44′, are brought intophysical contact (as represented in FIG. 3C) on an inner portion of thetwo-ply fabric portion.

As represented by FIG. 3C, the conductive yarn portions 30 and 30′ areon an outer surface portion 72 and the conductive float yarn portions 34and 34′ are on an inner surface portion 74 of the two-ply fabric.Similarly, as represented by FIG. 3C, the optional moisture retentiveyarn portions 46 and 46′, are on an outer surface portion 78 of thetwo-ply fabric. The conductive yarn portions 40 and 40′ are on outersurface portion 78, float yarn portions 44 and 44′ are all on an innersurface portion 76 of the two-ply fabric, as represented by FIG. 30.

Referring now to FIG. 3C, the folded over fabric portion 70 isrepresented as having surface portions 78 and 72, as well as twotextile-based electrodes, which are electrically continuous from surfaceportion 78 to surface portion 72. Such arrangement allows for thetransmission and reception of electrical signals between surfaceportions 72 and 78. Connection points 50 and 50′ can be adapted forsending or receiving such electrical signals.

A means for adapting 50 and 50′ for receiving and sending electricalsignals is represented with the aid of FIG. 4. In this figure, fabricportion 70 is represented from a view between surfaces 74 and 76, whichare facing one another as a result of folding 70 about horizontal axisAA′ (as shown in FIG. 3B). Surface 78 (the side adapted to be in contactwith a wearer's skin) contains conductive yarn portions 40 and 40′ andsurface 72 contains conductive yarn portions 30 and 30′. Betweensurfaces 76 and 74, conductive float yarn portions 44 and 44′ arebrought into physical contact with conductive float yarn portions 34 and34′, thereby providing electrical continuity between conductive yarnportions 40 and 40′ and conductive yarn portions 30 and 30′.

Electrically conductive contacts 50 and 50′ are respectively attached toconductive yarn portions 30 and 30′. Electrically conductive contacts 50and 50′ may be made of any electrically conductive material, such as,for example, metallic conductors. Electrically conductive contacts 50and 50′ can be attached to conductive yarn portions 30 and 30′ such thatthey communicate through 30 and 30′ and are capable of contacting orengaging with electrically conductive contacts 210 and 210′respectively. Electrically conductive contacts 210 and 210′ areassociated with 200, an electrical device.

Electrical device 200 is represented in FIG. 4 as being placed betweensurfaces 74 and 76 of the folded over fabric portion 70. As a result, anelectrical signal originating at conductive yarn portions 40 and 40′ canbe conducted directly to electrically conductive contacts 210 and 210′(as well as to 30 and 30′), respectively, which are each associated withelectrical device 200. Alternatively, an electrical signal originatingwith electrical device 200 may be conducted directly to electricallyconductive contacts 210 and 210′ (as well as to 30 and 30′), and thereonto conductive yarn portions 40 and 40′.

An embodiment including optional yarns 60 is shown in FIG. 4, where theoptional yarns 60 include, for example, PTFE filaments. The use ofoptional filaments 60 reduces the possibility of short circuiting of thetextile-based electrodes in garments expected to be worn by heavilyperspiring wearers. In one embodiment, the PTFE filaments can be wrappedabout or twisted with LYCRA® brand spandex yarns. Otherwise, these yarnsneed no special preparation and can be readily integrated with thetraditional textile filaments of the garment construction.

A portion of a wearable 110, fully integrated with two textile-basedelectrodes, is represented in FIG. 5. The wearable in FIG. 5 representsa sleeve, cuff, or band. In such an embodiment, the electrical device200 is capable of receiving, storing, and/or transmitting certainbiophysical parameters of a person or animal employing the wearable,fully integrated with textile-based electrodes.

As represented in FIG. 5, two textile-based electrodes can communicatedirectly with the electrical device 200, placed in a space formedbetween surfaces 72 and 74. The two conductive yarn portions 40 and 40′on the surface 78 are capable of contacting the skin of a wearer. As aresult of skin contact with 40 and 40′, any electrical signaloriginating from the wearer can be transmitted directly to 30 and 30′respectively, and, in turn, to electrical device 200, via the contacts50 and 50′. Similarly, electrical device 200 may be capable oftransmitting an electrical signal via contacts 50 and 50′ and, in turn,through conductive yarns 30 and 30′ and further in turn to conductiveyarns 40 and 40′, which contact the skin of the wearer and transmit thesame signal to the wearer.

In another embodiment of the invention, the electrical device 200 iscapable of biophysiological monitoring, such as sensing electricalsignals associated with the electrical activity of the heart the wearerand thus the number of heart beats per unit time. The electrical device200 can be engagable with contacts 50 and 50′, as represented in FIG. 4,using conductive contacts 210 and 210′. The snap-engaged contacts 50 and50′ suitable for this application can, for example, be 11 mm contacts,available from PRYM NEWEY Textiles Group, Whitecroft, Lydney,Gloucestershire, UK. Reinforcement fabrics can be provided under eachsnap 50, 50′, for example, in the form of a woven piece ofCORDURA/COOLMAX®. These can serve to reduce the wear and eventualfailure of the snaps located in the textile electrodes 30 and 30′.

The wearable 110 in FIG. 5 is in the form of a band that surrounds themid-thorax of the wearer (can also be placed at other parts of the bodye.g. wrist, arm, waist, etc.). The surface 78 of 110 is positionedtoward the wearer's body and conductive yarn portions 40′ and 40 arepositioned horizontally so as to receive electrical signals associatedwith the electrical activity of a beating heart.

Optionally, the signal pickup from the wearer's skin may be furtherenabled using a portion of yarn, such as cotton yarn 46, 46′ in FIG. 4,knitted into the fabric band portion surrounding 40 and 40′. Cottonyarns are known to be hydrophilic (as are, for example, silk, viscose,acetate and wool) and can promote the retention of body derived moisturein the vicinity of 40 and 40′.

It is also an option to provide a coating on or around the borders ofthe skin contacting electrodes 40 and 40′, which helps promote sweating,thus allowing moisture to build up immediately after donning thewearable 110. Such coating may, for example, be desirable inapplications where a wearer is not engaged in strenuous activity (inother applications, for example, where the wearer would be expected tobe engaged in more strenuous activity, such coating may be lessdesirable). Suitable coatings include, for example, LYCRA® T162C polymersolution (from INVISTA™ Technologies S. à. r. l., Wilmington, Del.19808) and ELASTOSIL R plus 573 electrically conductive silicone rubber(from Wacker Silicones, WACKER-CHEMIE GmbH, Germany).

A suitable electrical device to demonstrate the function of the heartrate monitor embodiment is made by POLAR Electro Oy, Professorintie 5,Finland, 90440 Kempele; and designated as S810i™ The POLAR S810i™includes an electronics module (200 in the embodiment represented byFIG. 5) and a wrist worn device that communicates via radio frequencywith the module. The wrist worn device logs the data of the wearer. Datacan be obtained during the wearer's activities, including, for example,strenuous activity like running, cycling, or skiing.

This embodiment of the invention can be superior to other means to weara device such as the POLAR S810i™ since there is the capability to fullyintegrate the device using textile-based electrodes with a fullfashioned garment. By comparison, chest worn belts and straps known foruse with the POLAR S810i™ are not as form fitting, comfortable, andunobtrusive. The provision of a garment, such as a knitted top or asports bra, fully integrated for biophysiological monitoring, can leadto a superior performing wearable embodiment of the invention.

Examples of wearables that can incorporate textile-based electrodesaccording to embodiments of the present invention include any type of agarment, including any type of a sports or athletic garment. Specificexamples of garments include shirts, tank tops, bras, and underwear.However, it is important to note that the wearable can also includebands, straps, belts, or any other form of wearable article. A one layerelectrode patch 40 can also be cut/sewn onto any wearable article.

Referring next to FIG. 13, a one piece infant's garment 130 is knittedor woven, and has a torso covering region 132, two arms 134, two legs136 and a neck band 138. A series of snaps 140 close the flap opening atthe torso covering region 132. The legs 136 terminate in bands 142 atthe leg openings. The arms 134 terminate in bands 144 at the armopenings. At least one band 146 is formed in the torso covering region132. One or more textile based electrodes 40, 40′ are formed in suchband 146. The textile based electrodes 40, 40′ have skin-contactingsurfaces that contact the infant's skin when the garment 130 is worn.The textile based electrodes 40 in FIG. 13 are the same as or comparableto textile based electrodes on wearable 110 shown in FIG. 5. Snaps 50,50′ form contacts for connection to an electrical device (not shown inFIG. 13).

Optionally, a second band 150 is formed in the torso covering region132. One or more textile based electrodes 40 a, 40 a′ are formed in suchband 150 and have snaps 50 a, 50 a′ for connection to an electricaldevice (not shown in FIG. 13).

In yet another optional embodiment, textile based electrodes 40 b, 40 b′with snaps 50 b, 50 b′ may be incorporated into the wrist band regionsof the garment 130. Such one-piece infant garment is more comfortablefor the infant. When snaps 50, 50′ are engaged to leads to a device,biophysical characteristics, such as heart rate, respiration rate, ECG,temperature for the infant may be transmitted to the device.

Referring next to FIG. 14, an alternate embodiment of the infant garment132 a incorporates textile based electrodes 40 c, 40 c′ into the ankleregions of the garment 130 a. The textile based electrodes 40 c, 40 c′include snaps 50 c, 50 c′ that may be engaged to leads for transmittingsignals to a device, so as to monitor biophysical characteristics of theinfant wearing the garment 132 a. Thus, an infant garment 130, 130 a mayhave textile based electrodes 40, 40 a, 40 b, 40 c positioned at thetorso, at one or more wrists and at one or more ankles as desireddepending upon the infant's biophysical characteristic to be monitored.

Another application for textile based electrodes incorporates suchelectrode(s) into a wrist band for remote monitoring of cardiacelectrical activity and/or pacemaker function. FIG. 7 shows a cardiacpatient remote monitoring system 300 in which two wrist worn electrodesor wrist bands 302 are linked by electrode leads 304 to a transmissiondevice 306. The transmission device 306 includes a telephone cradle 308for receiving a handset of a telephone (not shown in FIG. 7). Thetransmission device 306 permits voice and electronic data, such as ECGor EKG data, to be transmitted to a remote monitoring station, such as acardiac hospital data recovery system. A patient wears each of the wristbands 302 over a separate wrist to facilitate heart monitoring datacollection and transmission.

Referring next to FIG. 8, a wrist band 302 is shown as worn on apatient's wrist. The patient's wrist and hand are shown in phantomoutline in FIG. 8. The wrist band 302 incorporates a textile basedelectrode 40 that includes a connection or snap 50 for connecting to theelectrode lead 304 of FIG. 7. Snap 50 may be a 4 mm snap used as aconnector in many systems. Alternative connectors to link theelectrically conductive portions of the band to an electrode lead mightinclude pins, rivets or clamps.

FIGS. 9 and 10 show the wrist band 302 in more detail. The wrist band302 comprises a two layer construction. In one embodiment, the wristband 302 is formed from a circular knit fabric blank 309 into whichelectrode portions 314 and 316 are knitted. Alternate constructionsinclude various circular rib knit, cut and sew, weaving, and otherknitting.

Referring to FIG. 11, a circular knit blank 309 is formed in which afirst electrode portion 314 is a stripe of a width generally less thanthe width of the band to be formed that includes electrically conductiveyarns within the knit in such stripe. A second electrode portion 316 inthe circular knit blank 309 is a rectangular patch of dimensionsgenerally less than the width and circumference of the band to be formedand that includes electrically conductive yarns within the knit. Theremaining portions of the fabric in the blank 309 do not containelectrically conductive yarns and are not conducting portions. In apreferred embodiment, the nonconductive fabric of the blank 309 is aterry cloth structure with extending loops. Such terry cloth structurehas soft feel, enhanced band thickness and extra warmth. An alternatestructure includes a rib knit that is not terry cloth. These fabricconstructions are more comfortable than segmented metal bands heretoforeused with ECG monitoring systems.

The material content of the nonconductive portions of the wrist bandsmay include polypropylene fibers, acrylic fibers or polypropylene fibersor acrylic fibers blended with elastomeric fibers and/or cotton fibers.The conductive fabric of the stripe 314 and patch 316 of the blank 309may include one or more types of conductive fibers, such as but notlimited to, silver coated Nylon. In one example, a wrist band accordingto the invention contained from 25 to 35 percent by weight conductivefiber (such as silver coated Nylon), 30 to 40 percent by weightpolypropylene fiber, 10 to 20 percent by weight Nylon, 4 to 6 percent byweight LYCRA® spandex and 15 to 20 percent by weight other elastic.

The circular knit fabric blank 309 is then folded back upon itself andstitched by stitch line 328 at the selvages 326 a, 326 b (see FIGS. 11and 12) to form the two-layer circular band 302 (see FIGS. 9 and 10).

As shown in FIG. 10, the skin-contacting fabric surface 310 on the innerportion of the wrist band 302 comprises a continuous stripe 314 thatincorporates electrically conductive yarns to form a textile basedelectrode. The outer fabric surface 312 on the outer portion of thewrist band 302 comprises a patch 316 of electrically conductive yarns toform a textile based electrode. A snap or other connector 320 ispositioned in and through the patch 316 and provides means forconnecting the wrist band electrodes to the electrode leads 304 of thetransmission device 306. Stitches 318 through the two layers 310, 312hold the layers together and ensure good contact between the stripe 314and the patch 316 forming the textile electrode.

An alternate embodiment of the wrist band 302 a is shown in FIGS. 15 and16. In this alternate embodiment 302 a, the outer fabric surface 312 alacks the conductive patch (316 in FIGS. 9 and 10). Instead, connectoror snap 320 penetrates through both layers of fabric (outer fabric 312 aand inner fabric 310) to contact conductive stripe 314 on the innerfabric 310. As shown in FIG. 15, the mating male portion of the snap 320extends outwardly from the outer fabric surface 312 a and the flattersnap surface is found in contact with the stripe 314 on the inner fabricsurface 310.

Functional performance of textile based electrodes in a garment, wristband or infant garment can be evaluated indirectly by measuringelectrical resistance. A resistance of less than one Ohm between (i) thefarthest point of the textile based electrode in the garment or bandaway from the connector and (ii) the connector (often a snap) has beenfound to provide effective functional performance for a monitoring wristband or garment. Of course, individual garments, wrist bands or infantgarments may be field tested and adjusted individually for proper fit sothat biophysical signals, such as ECG, are clinically readable by arecording device.

Test Methods

In order to test the suitability of an embodiment falling within thescope of the present invention for use in biophysiological monitoring,the electrical conductivity between conductive textile yarns and anysignal pickup point (such as 50, 50′) must be established. In the caseof an inner electrode of conductive yarns (e.g. 40 and 40′), theresistance between them and signal pickup points 50, 50′ is measuredusing a FLUKE 180 series digital multimeter (from Fluke Electronics). Inpractice, a band of knit fabric, such as 70 in FIG. 5, is placed on amannequin the resistance measured.

Short circuits between the textile electrodes, due to sweating of thewearer, is measured using a mannequin as above and a wet band of knitfabric 70. The wetting agent used to wet the fabric is a 1% aqueous NaClsolution, which approximates the ionic conductivity of human sweatsecretions.

Represented in FIG. 6 are the dimensions a, b, c, d, e, f, and g of thetextile-based electrodes of FIG. 5. The distance between the metallicpick-up points 50 and 50′ is fixed at about 1.8 inches (46 mm) for eachexample.

Measurements of resistance are made between the textile electrodes 30and 30′, 40 and 40′, and from among all textile electrodes and metallicpickup points 50 and 50′.

Comparison measurements of heart rate monitoring using the POLAR S810i™electronics module and two different chest bands provided with the POLARmodule (e.g. the POLAR hard and soft bands) provide a test of thequality of the signal pickup. In general, the POLAR S810i™ module ismounted in an upper chest worn knit fabric band (i.e., 70, asrepresented in FIG. 5) for this comparison test. During a session ofstrenuous exercise, heart rate data is logged according to the methodsprovided by POLAR with the S810i™ module and wrist worn data logger.

EXAMPLES

Examples of the invention were made in the form of heart rate monitoringbelts (listed as 1-14 in Table 1). The heart rate monitoring belts weremade by circular knitting using a SMA-8-TOP1 seamless, 13 inch bodysize, knitting machine from SANTONI (from GRUPPO LONATI, Italy)(hereinafter, “the SANTONI knitting machine”). In making the heart ratemonitoring belts, a combination of different knitting constructions(including jersey and mock rib knit construction) using various types ofyarns were used. In each example, the denoted electrode region was madeusing Xstatic® yarns of a silver metallized nylon yarn of 70 denier and34 filaments from Laird Sauquoit Industries (Scranton, Pa., USA 18505)(hereinafter, “Xstatic® 70/34”).

In each of heart rate monitoring belts 1-14, a base fabric was firstconstructed. The yarn used to knit the base fabric in each belt wasCoolmax® 70/88 micro denier polyester yarn from INVISTA (“Coolmax®”),plated with Lycra® spandex (T-902C 260d). The Coolmax® and Lycra®spandex were knitted together using the SANTONI knitting machine at aratio of about 92% Coolmax® and 8% Lycra® spandex (ratios of from about75 to about 100% Coolmax® and from 0 to about 25% Lycra® spandex arealso possible), wherein both plain jersey stitching and mock rib (1×1,3×1, 2×1, 2×2) stitching were used in the regions of the fabriccontaining the textile-based electrodes (the “conductive regions”), aswell as the non-conductive regions of the fabric.

For the regions of the fabric containing the textile-based electrodes(or “conductive regions”), a conducive yarn was knitted on one side ofthe base fabric (on the non-float regions) using the SANTONI knittingmachine. The conductive yarn used in making heart rate monitoring belts1-14 was X-static® 70/34 (although composite yarns form Bekaert havingapproximately 80% polyester and 20% stainless steel could also be used).In this regard, conductive regions represented by 40, 40′, 30, and 30′(FIG. 3A) were knitted using plain jersey and mock rib stitch, and theconductive regions represented by 34, 34′, 44, and 44′ (FIG. 3A) wereknitted using float stitches (regions 40 and 40′ in FIG. 3A are alsorepresented as having dimensions a×b in FIG. 6).

Metallic snaps (50 & 50′ in FIG. 3A) were then installed to each of theheart rate monitoring belts 1-14 by first making small lead holes in thefabric (at positions 50 & 50′ in FIG. 3A). Next, a snap reinforcementmaterial having about a ½ inch diameter with a hole in the center (ofabout the same diameter as the corresponding small lead hole) was placedover positions 50 & 50′, such that the holes in the fabric and the holesin the snap reinforcement material approximately overlapped. The snapreinforcement material was made of a plain weave of Cordura® nylon &Coolmax®. Snaps were then added by inserting part 1 of a female snap(e.g. PRYM-DRITZ 12 mm) through each hole, attaching part 2 of thecorresponding snap on the other side of the fabric, and then rivetingthe snaps in place.

In the heart rate monitoring belts 1-14, the dimensions of regions 40and 40′ (FIG. 3A), i.e., a×b (FIG. 6), varied, as shown in Table 1. Inaddition, in the heart rate monitoring belts 1-14, the distance shown aswidth c in FIG. 6 varied, as shown in Table 1.

In heart rate monitoring belts 1 through 4, the snaps were placed suchthat electrically conductive contacts 210 and 210′ in FIG. 4 were facingtowards the skin (so that the electronic device 200 in FIG. 4 wasoutside the heart rate monitoring belt).

In heart rate monitoring belts 5 through 14, the snaps were placed suchthat electrically conductive contacts 210 and 210′ in FIG. 4 were facingaway from the skin (so that the electronic device 200 in FIG. 4 wasinside the heart rate monitoring belt).

In addition, heart rate monitoring belts 11 through 14 included ahydrophilic yarn portion of cotton yarns (represented by dimensions d×ein FIG. 6) around each electrode portion (represented by dimensions a×bin FIG. 6). This hydrophilic yarn portion (shown as 46 and 46′ in FIG.3B) was knitted on to the opposite side of the fabric as the conductiveregions (shown as 40 and 40′ in FIG. 3A). The dimensions of d×e forheart rate monitoring belts 11 through 14 are shown in Table 1.

Examples 12 and 14 of the invention also included a hydrophobic portionof yarns (represented as width g in FIG. 6). The material used in thishydrophobic portion was made up of about 90% PTFE 100d and about 10%Lycra® spandex and was knitted separately using a Lawson tube knittingmachine (Made by Lawson-Hemphill Model # FAKSE). A band of this materialwas then cut and stitched in between the conductive regions, as shown inFIG. 6. The width of g for heart rate monitoring belts 12 and 14 isshown in Table 1.

Two fundamental measurements were made on the example heart rate monitorbelts 1 through 14. These measurements included: (1) the dry resistancebetween skin contacting electrode portions (40 and 40′) and the metallicsnaps 50 and 50′; and (2) the water wetted (1% aqueous NaCl solution)resistance between the metallic snaps 50 and 50′.

For comparison purposes, the POLAR S810i “soft” belt was used forComparative Example 1 and a POLAR S810i “hard” belt was used forComparative Example 2. Each of these was tested along with thetextile-based electrodes of the invention.

In the case of Comparative Example 1, the resistance was measured fromthe body contacting electrode to the snap which engaged the POLAR S810imodule. This measurement was not made for Comparative Example 2 (as itis fully integrated).

The quality of signal pick-up was rated by a panel of experts in usingthe POLAR S810i. The signal quality of the POLAR belts was first ratedfor speed of first signal acquisition during the onset of a prescribedexercise routine for each wearer. The presence of noise or other signaldegradation was also noted. A score of 10 was considered excellent and ascore of 1 was considered poor. Where more than one score was reported,the measurement was a repeat measurement.

Table 1 provides a summary of heart rate monitoring belts 1-14 as wellas Comparative Examples 1 and 2. The form of the heart rate monitoringbelts was substantially as represented in FIG. 5.

TABLE 1 Wet Signal Example a × b C d × e g Resistance Resistance QualityNo. *(inches) *(inches) *(inches) *(inches) (ohms) (kOhms) Rating Comp 13.0 × 0.8 4.2 N/A N/A 9 N/A 6 Comp 2 2.8 × 0.6 4.0 N/A N/A N/A N/A 7 13.3 × 0.7 4.9 N/A N/A 4 4 N/A 2 3.3 × 0.7 5.5 N/A N/A 4 4 6 3 3.3 × 0.75.4 N/A N/A 5 4 3 4 3.3 × 0.7 5.7 N/A N/A 9 4 5 5 3.3 × 0.7 4.2 N/A N/A8 N/A 6 6 3.3 × 0.7 4.2 N/A N/A 8 6 N/A 7 3.3 × 0.7 4.6 N/A N/A 6 3 N/A8 3.3 × 0.7 4.7 N/A N/A 6 2   3.3 9   5 × 1.2 4.7 N/A N/A 7 2 N/A 10   5 × 1.2 4.7 N/A N/A 7 2 N/A 11    4 × 1.1 4.7 4.3 × 2.3 N/A 4 2 7, 8,**(3) 12    4 × 1.1 4.0 4.3 × 2.3 0.7 3 7 N/A 13  3.5 × 0.9 4.0 3.8 ×1.8 N/A 4 2 7, 8, **(3) 14  3.5 × 09  4.0 3.8 × 1.8 0.7 3 64  N/A *[1inch is equivalent to 25.4 mm] **[repositioned electrode test]

1. A biophysical data monitoring system, comprising: a first fabricportion comprising a skin contacting surface and an inner surface andthat includes non-conductive yarns and at least one electricallyconductive region comprising stretch recovery electrically conductiveyarns or yarn filaments; a second fabric portion comprising an outersurface and an inner surface, and that includes non-conductive yarns,wherein the second fabric portion overlays at least a portion of thefirst fabric portion; and a connector for connecting the at least oneelectrically conductive region of the first fabric portion to abiophysical data monitor or to a lead for such monitor for transmittingsignals representing biophysical data.
 2. The biophysical datamonitoring system of claim 1, wherein the first fabric portion and thesecond fabric portion are formed from a single fabric and wherein thesecond fabric portion overlays the first fabric portion upon folding thesingle fabric.
 3. The biophysical data monitoring system of claim 1,wherein the second fabric portion includes at least one electricallyconductive region comprising stretch recovery electrically conductiveyarns or yarn filaments, wherein the second fabric portion overlays atleast a portion of the first fabric portion and the at least oneelectrically conductive region of the second fabric portion contacts theat least one electrically conductive region of the first fabric portion.4. The biophysical data monitoring system of claim 3, wherein at leastone of: (i) the electrically conductive region of the first fabricportion; and (ii) the electrically conductive region of the secondfabric portion; comprises at least a portion of an elastifiedelectrically conductive yarn.
 5. The biophysical data monitoring systemof claim 3, wherein at least one of: (i) the electrically conductiveregion of the first fabric portion; and (ii) the electrically conductiveregion of the second fabric portion; comprises an elastic yarn at leastpartially plated with a conductive yarn.
 6. The biophysical datamonitoring system of claim 3, wherein the first and second fabricportions are of a knit construction, and the electrically conductiveregion of the first fabric portion includes one or more float yarns. 7.The biophysical data monitoring system of claim 3, wherein the connectoris directly connected to the at least one electrically conductive regionof the second fabric portion and is indirectly connected to the at leastone electrically conductive region of the first fabric portion throughthe second fabric portion.
 8. The biophysical data monitoring system ofclaim 1, wherein the connector is selected from the group consisting of:snap, rivet, pin and clamp.
 9. The biophysical data monitoring system ofclaim 1, wherein the biophysical data is selected from the groupconsisting of: heart rate, electrocardiogram signal, pacemaker signal,and respiration rate.
 10. A wearable article for monitoring biophysicalcharacteristics of a person or animal wearing such article, comprising:a first fabric portion comprising a skin contacting surface and an innersurface and that includes stretch-recovery non-conductive yarns and atleast one electrically conductive region comprising stretch-recoveryelectrically conductive yarn filaments; a second fabric portioncomprising an outer surface and an inner surface, and that includesstretch-recovery non-conductive yarns and at least one electricallyconductive region comprising stretch-recovery electrically conductiveyarn filaments, wherein the second fabric portion overlays at least aportion of the first fabric portion and the at least one electricallyconductive region of the second fabric portion contacts the at least oneelectrically conductive region of the first fabric portion; and aconnector for connecting at least one of (i) the at least oneelectrically conductive region of the first fabric portion or (ii) theat least one electrically conductive region of the second fabric portionto a device or a lead to a device for receiving signals transmittedwhich represent biophysical data.
 11. The wearable article of claim 10,wherein the connector is selected from the group consisting of: snap,rivet, pin and clamp.
 12. The wearable article of claim 10, wherein atleast one of: (i) the electrically conductive region of the first fabricportion; and (ii) the electrically conductive region of the secondfabric portion; comprises an elastic yarn at least partially plated witha conductive yarn.
 13. The wearable article of claim 10, wherein atleast one of (i) the electrically conductive region of the first fabricportion; or (ii) the electrically conductive region of the second fabricportion, comprises one or more float yarns.
 14. The wearable article ofclaim 13, wherein (i) the electrically conductive region of the firstfabric portion; and (ii) the electrically conductive region of thesecond fabric portion, both comprise float yarns that are stitchedtogether.
 15. A textile-based system for receiving or transmittingelectrical signals, comprising: a first fabric portion comprising acontacting surface and an inner surface and that includes non-conductiveyarns and at least one electrically conductive region comprising stretchrecovery electrically conductive yarns or yarn filaments; a secondfabric portion comprising an outer surface and an inner surface, andthat includes non-conductive yarns, wherein the second fabric portionoverlays at least a portion of the first fabric portion; and means forsending electrical signals to the first fabric portion or for receivingelectrical signals from the first fabric portion.
 16. The textile-basedsystem of claim 15, wherein the means for sending electrical signals tothe first fabric portion or receiving signals from the first fabricportion comprises at least one connector for connecting the at least oneelectrically conductive region of the first fabric portion directly orindirectly to at least one of (i) a receiving device for receivingelectrical signals transmitted in response to movement of the firstfabric portion, or (ii) a lead to a receiving device for receivingelectrical signals transmitted in response to movement of the firstfabric portion, or (iii) a transmitting device for transmittingelectrical signals to the first fabric portion, or (iv) a lead to atransmitting device for transmitting electrical signals to the firstfabric portion.
 17. The textile-based system of claim 16, wherein theconnector is selected from the group consisting of: snap, rivet, pin andclamp.
 18. The textile-based system of claim 16, wherein the connectorconnects to the electrically conductive region of the first fabricportion indirectly through the second fabric portion.
 19. Thetextile-based system of claim 15, wherein the first fabric portion andthe second fabric portion are formed from a single fabric and whereinthe second fabric portion overlays the first fabric portion upon foldingthe single fabric.
 20. The textile-based system of claim 15, wherein thesecond fabric portion includes at least one electrically conductiveregion comprising stretch recovery electrically conductive yarns or yarnfilaments, wherein the second fabric portion overlays at least a portionof the first fabric portion and the at least one electrically conductiveregion of the second fabric portion contacts the at least oneelectrically conductive region of the first fabric portion.